Method for monitoring an individual&#39;s motor load and insole for the implementation thereof

ABSTRACT

A method for measurements of parameters characterizing human motor activity provides registration of signals generated by load sensors mounted in shoe insoles, with each insole having at least two load sensors, one mounted near the heel, and the other near the toe of the foot. The specific type of motor activity is determined based on temporal correlation of load sensor signals from both insoles and values thereof. Person&#39;s weight, including additionally carried weight, is determined by summing up signal values from said load sensors, with the specific type of motor activity considered; thereafter, person&#39;s motor stress is determined based on specified type of motor activity and person&#39;s weight, including additionally carried weight. The method enables a real-time monitoring of motor stress of a person at different types of motor activity, e.g. running, walking at different pace, standing, with person&#39;s weight, including additionally carried weight, taken into consideration.

RELATED APPLICATIONS

This Application is a Continuation Application of U.S. non-provisionalapplication Ser. No. 14/832,002 filed on Aug. 21, 2015, which in turn isa Continuation Application of International ApplicationPCT/RU2014/000137, filed on Mar. 4, 2014, which in turn claims priorityto Russian Patent Applications No. RU2013110572, filed Mar. 5, 2013, allof which are incorporated herein by reference in their entirety.

FIELD OF INVENTION

The invention relates to the field of monitoring parameters measurementsof human motor activity, in particular, to motor stress measurementsusing load sensors disposed in a shoe insole.

BACKGROUND OF THE INVENTION

Various methods are known for measuring human motion parameters by meansof load sensors located in shoe insoles.

Patent KR 100792327 (publication date Dec. 31, 2007; IPC A43B3/00,A43B5/00), for instance, describes a method for measuring player'sweight and displacement of his bodily center of gravity at golfing bymeans of piezoelectric sensors placed under shoe insoles. Measurementsof force acting upon the sensor at golfing render it possible to obtaina real-time assessment of player's motion pattern and motion performanceaccuracy. However, this method provides no means for measuring humanmotor stress during the game.

International patent application WO 2001/035818 (publication date May25, 2001; IPC A61B5/103) describes a method for measuring the forcegenerated by athlete's legs at long and high jump, in games, or atleisure. The force is measured by at least one load sensor located in ashoe insole. A transceiver with antenna and a power supply are mountedin the shoe to provide the transmission of measured data to an externalprocessing unit. However, this method does not allow for assessment ofhuman motor stress during sporting activities based on signals from loadsensors.

The concept of patent FR 2873281 (publication date Jul. 26, 2004; IPCA43B3/00, A43B5/00, A61B5/103) is the closest to the one claimed here;it describes sporting shoes having a measuring device to determinephysical parameters of motion and calculate human motor stress thereby.The shoes are equipped with load sensors disposed underneath human foot,and a computing unit with display for showing the information related tohuman motor stress. Measurements of physical parameters by such a deviceallow a person's walking pattern to be identified; whereat saidparameters include: pace, velocity, acceleration, distance covered,travel time, rate of bodily metabolism and other parameters related toenergy consumption, such as total amount of energy burned by the person.This enables a general monitoring of human motor stress. However, suchan evaluation of motor stress ignores additional motor weight, i.e.weight carried at walking, running or other type of motor activity,which is generally a variable value throughout the period of monitoring.All the above leads to incorrect assessments of motor stress orrestricts the applicability of this method. Furthermore, this methodenables measurements of only walking stress and cannot be applied toother types of motor activity, for example running

The technical problem to be solved by the present invention is thedevelopment of a method to assess human motor stress in real time, withperson's body weight, including additionally carried weight, taken intoaccount; said method being applicable to various types of motoractivity, such as running, walking at various pace, as well as standing.

SUMMARY OF THE INVENTION

One of the objects of the present invention is a method of monitoringmotor stress of a person, wherein signals generated by load sensorsmounted in shoe insoles are registered; whereat each insole has two loadsensors: a first load sensor being disposed in the heel region and thesecond sensor being disposed in the toe region of the foot. The specifictype of motor activity is identified based on time relationship of loadsensor signals from both insoles and the values of the signals. Theweight of the human, as well as additionally carried weight, isdetermined by summing up the load sensor signals and by the type of thedetermined motor activity. Thereafter, the motor stress is determinedbased on the type of motor activity and the body weight, includingadditionally carried weight.

When running or walking, a human moves feet alternately, first one, thenthe other. The load sensors located in the heel region and in the toeregion make it possible to determine the duration of the foot's contactwith the base (support phase) and the duration of stride (stride phase)within one walking or running cycle. Since different types of motoractivities are characterized by different time relationship of thesupport time and the stride time, that time relationship (temporalcorrelation) of load sensor signals from different insoles permits todetermine the pattern or the type of motor activity that needs to beidentified.

The inventive method provides for the determination of the motor stressof a human based on both the type of motor activity (walking, running,etc.) and the weight of the human, including additionally carriedweight. The weight plus the additionally carried weights are measureddirectly in the process of the motor activity. Thus, the motor stress ofthe human in a particular situation can be measured much moreaccurately, and monitoring that stress can be performed more effectivelyover a specified time period.

In particular embodiments of this method, identification of varioustypes of motor activity becomes feasible according to the proceduredescribed below.

Such type of motor activity as walking is determined if the values ofthe signals from the load sensors in both insoles exhibit periodicvariations of the values of the signals, and the signals from the loadsensors from different insoles partially overlap in time.

Such type of motor activity as running is determined if the values ofthe signals from the load sensors in both insoles exhibit periodicvariations of the values of the signals, and the signals from the loadsensors from different insoles do not overlap in time.

Such type of motor activity as standing is determined if the values ofthe signals from the load sensors in both insoles exhibit periodicvariations of the values of the signals, and the signals from the loadsensors from different insoles overlap in time.

The inventors have obtained a series of empirical relationships thatpermit to determine the weight of a human, including additionallycarried weight, with the specific type of motor activity taken intoaccount.

For example, weight P, including additionally carried weight, of a humanwho is walking at a slow pace of 60 steps per minute can be determinedas follows:

P=K _(W) ·F,

where: K_(W) is a calibration factor determined for a specific personwith a known weight at walking;

F is the mean value of a foot pressure force over one walking cycle,wherein:

F=(F_(1max) +F _(2 max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2 max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole,

wherein one cycle consists of two consecutive steps made by one foot andthen the other.

The weight, including additionally carried weight, of a human who iswalking at a pace of 60 or more steps per minute can be determined asfollows:

P=K _(w) ·F·(1010−1.2·V−0.026·V ²)·0.001,

where: K_(W) is a calibration factor for a given person with a knownweight who is walking at a pace of up to 60 steps per minute;

F is the mean value of a foot pressure force over one walking cycle,wherein:

F(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole;

V is the number of steps per minute,

wherein one cycle consists of two consecutive steps made by one foot andthen the other.

The weight, including additionally carried weight, of a running humancan be determined by formula:

P=K _(R) ·F·(1090−4.4·V−0.045·V ²)·0.001,

where: K_(R) is a calibration factor for a given person with the knownweight at running;

F is the mean value of a foot pressure force over one running cycle,wherein:

F=(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole;

V is the number of steps per minute,

wherein one running cycle consists of two consecutive steps made by onefoot and then the other.

The weight, including additionally carried weight, of a standing humancan be determined by formula:

P=K _(S) F,

where: K_(S) is a calibration factor to be determined for a given humanwith a known weight at standing;

F is the mean value of foot pressure force over the period of standing,wherein:

F=(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole;

In particular, the motor stress at walking E_(W) can be determined byformula:

${E_{W} = {e_{W}{\sum\limits_{i = 1}^{w}\; {P_{i} \cdot T_{i}}}}},$

where: i is the number of time interval committed to walking activity;

w is the number of time intervals committed to walking activity;

P_(i) is the weight of the human, including additionally carried weight,(in kg) registered within i-th time interval;

T_(i) is the duration of i-th time interval (in min.);

e_(W) is specific energy input to walking activity, in kcal per kg ofweight per minute, expressed as follows:

e _(w) =k _(per)·(25-0.13·V+0.022·V ²+0.00038·V ³+0.0000021·V ⁴),

where: k_(per) is an individual factor for a given person/human, to bedetermined in advance;

V is a number of steps per minute.

In particular, the motor stress at running E_(R) can be calculated byformula:

${E_{R} = {e_{R}{\sum\limits_{i = 1}^{r}\; {P_{i} \cdot T_{i}}}}},$

where: i is the number of time interval committed to running activity;

r is the number of time intervals committed to running activity;

P_(i) is the weight of the human, including additionally carried weight,(in kg) registered within i-th time interval;

T_(i) is the duration of i-th time interval (in min.);

e_(R) is specific energy input to running activity, in kcal per kg ofweight per minute, determined as follows:

e _(R) =k _(per)·(73−2.2·V+0.051·V ²+0.000335·V ³+0.00000077·V ⁴),

where: k_(per) is an individual factor for a given person, to bedetermined in advance;

V is a number of steps per minute.

In particular, the motor stress at standing E_(S) can be determined byformula:

${E_{S} = {e_{S}{\sum\limits_{i = 1}^{s}\; {P_{i} \cdot T_{i}}}}},$

where: i is the number of time interval committed to standing activity;

s is the number of time intervals committed to standing activity;

P_(i) is the weight of the person, including additionally carriedweight, (in kg) registered within i-th time interval;

T_(i) is the duration of i-th time interval (in min.);

e_(S) is specific energy input to standing activity, in kcal per kg ofweight per minute, determined as follows:

e _(S) =k _(per)·25,

k_(per) is an individual factor for a given person, to be determined inadvance;

In a particular embodiment of the method, in addition to the signals ofthe first and second load sensors, signals from additional load sensorsdisposed in each insole along the trajectory of a support reaction forceat walking between the first load sensor and the second load sensor aredetected. The signals from the additional sensors used for calculationstogether with the signals from the first and second load sensors. Thisallows a more accurate measurement of the weight of a human, as well asadditionally carried weight.

Another object of the present invention is an insole designed forimplementing the described method. The insole comprises at least a firstload sensor mounted near the heel of the foot and a second load sensormounted near the toe of the foot, both capable of generating signalsthat register the pressure force applied by the foot of human.

Additionally, the insole may be equipped, at least, with ananalog-to-digital converter and transceiver to convert the signals fromload sensors to digital form and transmit them to an external processingunit.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention is illustrated by the following drawing figures:

FIG. 1 is a schematic illustration of the design of the insole with loadsensors mounted therein; shown here are both, left and right insoles andlocation of load sensors relative to the trajectory of support reactionforce at walking.

FIG. 2 is a wiring diagram of an exemplary measuring device forregistering the force applied by foot upon load sensors mounted ininsoles, as shown in FIG. 1—each load sensor constitutes a straintransducer with four bridge-connected strain gages.

FIG. 3 shows exemplary timing diagrams which illustrate the temporalrelationship of load sensor signals from both insoles as registered bythe circuit shown in FIG. 2 at standing activity.

FIG. 4 shows exemplary timing diagrams which illustrate the temporalrelationship of load sensor signals from both insoles as registered bythe circuit shown in FIG. 2 at walking activity.

FIG. 5 shows exemplary timing diagrams which illustrate the temporalrelationship of load sensor signals from both insoles as registered bythe circuit shown in FIG. 2 at running activity.

FIG. 6 shows a circuit diagram of another exemplary measuring device forregistering the force applied by foot upon load sensors placed ininsole, as shown in FIG. 1. In this embodiment, each load sensorconstitutes a piezoelectric transducer.

FIG. 7 shows exemplary timing diagrams which illustrate the temporalrelationship of load sensor signals from both insoles as registered bythe circuit shown in FIG. 6 at walking activity.

FIG. 8 shows exemplary timing diagrams which illustrate the temporalrelationship of load sensor signals from both insoles as registered bythe circuit shown in FIG. 6 at running activity.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The present invention is illustrated by the following embodiments ofinsoles with load sensors in the form of strain gages and piezoelectrictransducers.

In the first embodiment, each insole 1 (see. FIG. 1) includes a firstload sensor 2 located in the heel region of the foot, a second loadsensor 3 located in the toe region of the foot, and two additional loadsensors 4 located actually on the trajectory 5 of support reaction forceat walking. FIG. 2 shows an embodiment of a schematic diagram of device6 for registering the force applied upon load sensor by foot. In thisembodiment, load sensors 2-4 are represented by strain transducers(strain gauges) 7, each consisting of four bridge-connected strain gages8. One bridge diagonal is connected to power supply 10, while the otheris connected to input/output ports of microcontroller 9 in such a waythat all four strain transducers 7 (first load sensor 2, second loadsensor 3, and two additional load sensors 4) are eventually connected toeight input/output ports L1-L8 of microcontroller 9 which registersanalog signals from strain transducers 7 and converts said signals todigital form. Antenna output G of microcontroller 9 with a built-intransceiver is connected to antenna 11. Device 6 is energized by powersupply 10. Microcontroller 9 is switched on by commands from an externalcomputer (not shown in the drawings). The external computer is mountedin a man-portable device and is capable of determining motor stress.

The method of motor stress monitoring according to the present inventionis implemented as follows.

The type of motor activity is determined based on signals from straingages 7 (load sensors 2-4) of both insoles 1 registered by signalprocessing unit 6 and time relationship of signals from strain gages 7on left and right insoles 1.

For example, such activity as standing is distinguished by signals shownin FIG. 3, where graph (a) corresponds to signal F₁ from strain gage 7of insole 1, while graph (b) corresponds to signal F₂ from strain gage 7of the other insole 1. At this type of motor activity signals F₁ and F₂from strain gages 7 of both insoles 1 are essentially equal in value andfeature almost complete overlap in time. FIG. 3 shows that signal F₁from strain gage 7 of insole 1 (graph (a)) is greater in value thansignal F₂ from strain gage 7 of the other insole 1 (graph (b)). It meansthe person is standing leaning on one leg more than the other.

Such type of motor activity as walking is distinguished by signals shownin FIG. 4, where graph (a) corresponds to signal F₁ from strain gage 7of insole 1, while graph (b) corresponds to signal F₂ from strain gage 7of the other insole 1. This type of motor activity is characterized byalternating changes in signal values F₁ and F₂ from strain gages 7 ofboth insoles 1 and by availability of partial overlap in time (overlaptime interval T_(L)).

Such type of motor activity as running is distinguished by signals shownin FIG. 5, where graph (a) corresponds to signal F₁ from strain gage 7of insole 1, while graph (b) corresponds to signal F₂ from strain gage 7of the other insole 1. This type of motor activity is characterized byalternating changes in signal values F₁ and F₂ from strain gages 7 ofboth insoles 1 and by absence of time overlap of said signals.Conversely, a time gap designated as time interval T_(D) is observedbetween said signals.

The availability of at least two load sensors in each insole: firstsensor 2 near the heel and second sensor 3 near the toe, makes itpossible to define not only the above-mentioned types of motor activity(walking, running, standing), but also other types of activity likesitting, cycling, skiing. However, this method covers only those typesof motor activity, in which person's weight, including additionallycarried weight, is transmitted to his/her feet.

Table 1 below matches values of load sensor signals and their temporalrelationship to a certain type of motor activity (with at least twosensors in one insole).

TABLE 1 Load sensor signal values from both insoles Type of human motorand their temporal relationship activity Not available Sitting, lying,with shoes removed Essentially invariable values and almost completeStanding time overlap Partial overlap at cyclic repetition Walking Nooverlap at cyclic repetition Running Cyclic and essentially simultaneousvariation of Jumping sensor signal values from both insoles

Similar signals from load sensors 2, 3, and 4 used to determine(identify) the type of person's motor activity can be also used tomeasure person's weight, including additionally carried weight. The term“additionally carried weight” means extra weight borne by a person,e.g., carried items or special training weights. At that, person'sweight must be determined in advance, because the method according tothe present invention involves human motor stress monitoring whichrequires that both the type of motor activity and person's weight,including the weight additionally carried during this activity, be takeninto consideration.

The mathematical relationships related to types of motor activity thatwere empirically obtained by the inventors can be used for measuringperson's weight, including additionally carried weight.

Thus, at standing activity the weight measurement is reduced basicallyto the summation of signal values from all load sensors 2-4 of bothinsoles.

Person's weight, including additionally carried weight, at standing canbe expressed as follows:

P=K _(S) ·F,

where: K_(S) is a calibration factor to be determined for a given personwith a known weight at standing;

F is the mean value of pressure force of feet at standing. It can bedetermined for a certain period of time, e.g., from 5 to 10 seconds,wherein:

F=(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole;

Calibration factor K_(S), as well as other calibration factors used incalculations of person's weight at walking or running, can be determinedin the process of system calibration. At the same time, they can also bedetermined directly during monitoring, when the person is known to carryno additional weight at this point in time, i.e., load sensors take uponly person's known sole weight.

At slow walking pace of up to 60 steps per minute, person's weight P,including additionally carried weight, can be calculated using formula:

P=K _(W) ·F,

where: K_(W) is a calibration factor to be determined for a walkingperson with known weight;

F is the mean value of foot pressure force over one walking cycle,wherein:

F=(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2 max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole,

whereat one cycle is assumed to consist of two consecutive steps made byone foot and the other.

At walking pace of 60 or more steps per minute, person's weight,including additionally carried weight, can be found by formula:

P=K _(W) ·F·(1010−1.2·V−0.026·V ²)·0.001,

where: K_(W) is a calibration factor to be determined for a given personwith known weight, who is walking at pace of up to 60 steps per minute;

F is the mean value of foot pressure force over one walking cycle,wherein:

F=(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole;

V is the number of steps per minute,

whereat a cycle is assumed to consist of two consecutive steps with onefoot and the other.

The weight, including additionally carried weight, of a person atrunning can be determined by formula:

P=K _(R) ·F·(1090−4.4·V−0.045·V ²)·0.001,

where: K_(R) is a calibration factor, which is determined for a givenperson with known weight at running;

F is the mean value of foot pressure force over one running cycle,wherein:

F=(F _(1max) +F _(2max))/2,

where: F_(1max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of one insole;

F_(2max) is the maximum value of summarized foot pressure forcesregistered by all load sensors of the other insole;

V is the number of steps per minute at a given running pace,

whereat one running cycle is assumed to consist of two consecutive stepsmade by one foot and the other.

The motor stress, with type of motor activity and person's weight,including additionally carried weight, considered, is determined asfollows.

Motor stress at walking E_(W) is found by formula:

${E_{W} = {e_{W}{\sum\limits_{i = 1}^{w}\; {P_{i} \cdot T_{i}}}}},$

where: i is the serial number of time interval committed to walkingactivity;

w is the number of time intervals committed to walking activity;

P_(i) is person's weight, including additionally carried weight,registered within i-th time interval (in kg);

T_(i) is duration of i-th time interval (in min.);

e_(S) is specific energy input to walking activity, in kcal per kg ofweight per minute, determined as follows:

e _(W) =k _(per)·(25−0.13·V+0.022·V ²+0.00038·V ³+0.0000021·V ⁴),

where: k_(per) is an individual factor for a given person, to bedetermined in advance;

V is the number of steps per minute at a given walking pace.

Factor k_(per) can be determined, for example, as described in: Kotz, Y.M. Sports Physiology. Moscow: Physical Culture and Sport, 1998, p. 69,and can range from 0.6 to 1.1. The values that k_(per) can take forpeople of different age are shown in Table 2 below.

TABLE 2 20-29 30-39 40-49 50-59 over 60 years years years years yearsFor males 1.07 1.0 0.93 0.82 0.64 For females 0.94 0.81 0.77 0.68 0.61

Motor stress of a person at running E_(R) is as follows:

${E_{R} = {e_{R}{\sum\limits_{i = 1}^{r}\; {P_{i} \cdot T_{i}}}}},$

where: i is the serial number of time interval committed to runningactivity;

r is the number of time intervals committed to running activity;

P_(i) is person's weight, including additionally carried weight, (in kg)registered within i-th time interval;

T_(i) is duration of i-th time interval (in min.);

e_(R) is specific energy input to running activity, in kcal per kg ofweight per minute, determined as follows:

e _(R) =k _(per)·(73−2.2·V+0.051·V ²+0.000335·V ³+0.00000077·V ⁴),

where: k_(per) is an individual factor for a given person, to bedetermined in advance;

V is the number of steps per minute at a given running pace.

Motor stress of a person at standing E_(S) can be expressed as:

${E_{S} = {e_{S}{\sum\limits_{i = 1}^{s}\; {P_{i} \cdot T_{i}}}}},$

where: i is the serial number of time interval committed to standingactivity;

s is the number of time intervals committed to standing activity;

P_(i) is person's weight, including additionally carried weight, (in kg)registered within i-th time interval;

T_(i) is duration of i-th time interval (in min.);

e_(S) is specific energy input to standing activity, in kcal per kg ofweight per minute, determined as follows:

e _(S) =k _(per)·25,

where k_(per) is an individual factor for a given person, to bedetermined in advance;

Another embodiment of device 12 for implementing this method usingpiezoelectric transducers as load sensors is shown in FIG. 6. Similarlyto the preceding embodiment, right and left insoles 1 (see FIG. 1)include first load sensor 2 located near the heel, second load sensor 3located near the toe, and two additional sensors 4 located essentiallyalong the trajectory 5 of support reaction force at walking. Loadsensors 2, 3, and 4 in this embodiment consist of piezoelectrictransducers 13, 14, and 15, respectively, connected via matchingresistors R1-R8 to input/output ports L1-L4 of microcontroller 9.Similarly to the embodiment shown in FIG. 2, antenna output G ofmicrocontroller 9 is connected to antenna 11.

The method of motor stress monitoring based on the use of piezoelectrictransducers as load sensors is implemented as follows.

Similarly to the first embodiment of the inventive method, signals fromload sensors 2, 3, and 4 of each insole 1 represented here bypiezoelectric transducers 13, 14, and 15, respectively, are registered.FIG. 7 shows exemplary timing diagrams which illustrate the temporalrelationship of load sensor signals (e.g., piezoelectric transducers 13)from both insoles at walking, whereas FIG. 8 shows the same at runningContrary to the embodiment with strain transducers 7 (see FIG. 4 andFIG. 5), signals from the piezoelectric transducers, given theirinherent amplitude-frequency response, are shaped as distinctive spikescorresponding to the moment the foot pressure is applied topiezoelectric transducer and released from said transducer (a signal ofreverse polarity). The availability of spikes with opposing polaritiesmakes it possible to reconstruct the signal corresponding to theduration of support phase, and, similarly to the preceding example,determine temporary relationships of signals from piezoelectrictransducers of both insoles.

Thus, such type of motor activity as walking is characterized by signalsshown in FIG. 7, where graph (a) corresponds to signal F₁ frompiezoelectric transducer 13 (also known as sensor 2) of one insole 1,and graph (b) corresponds to signal F₂ from piezoelectric transducer 13(also known as sensor 2) of the other insole 1. Graphs (c) and (d) inFIG. 7 show signals P₁ and P₂ corresponding to the duration of footpressure on piezoelectric transducers 13 of one insole and other insole1, respectively. The rising edge of signals P₁ and P₂ in graphs (c) and(d) of FIG. 7 correlates with signals F₁ and F₂ of positive polarity ingraphs (a) and (b) of FIG. 7, respectively, while the falling edge ofsignals P₁ and P₂ in graphs (c) and (d) of FIG. 7 correlates withsignals F₁ and F₂ of negative polarity in graphs (a) and (b) of FIG. 7,respectively. Such type of motion activity as walking is characterizedby alternating variation of signal values shown in graphs (c) and (d),and by availability of their partial overlap (overlap time intervalT_(L)).

Similarly, such type of motor activity as running is characterized bysignals shown in FIG. 8, where graph (a) corresponds to signal F₁ frompiezoelectric transducer 13 (also known as sensor 2) of one insole 1,and graph (b) corresponds to signal F₂ from piezoelectric transducer 13(also known as sensor 2) of the other insole 1. Graphs (c) and (d) inFIG. 8 show signals P₁ and P₂ corresponding to the duration of footpressure on piezoelectric transducers 13 of one insole and other insole1, respectively. The rising edge of signals P₁ and P₂ in graphs (c) and(d) of FIG. 8 correlates with signals F₁ and F₂ of positive polarity ingraphs (a) and (b) of FIG. 8, respectively, while the falling edge ofsignals P₁ and P₂ in graphs (c) and (d) of FIG. 8 correlates withsignals F₁ and F₂ of negative polarity in graphs (a) and (b) of FIG. 8,respectively. Such type of motion activity as running is characterizedby alternating variation of signal values shown in graphs (c) and (d)with no overlap in time. Conversely, a time gap designated as timeinterval T_(D) between these signals is observed.

To measure person's weight, including additionally carried weight, themathematical relations from the first embodiment of the the presentinvention can be applied. In this case, maximum values of signals F₁

F₂ from piezoelectric transducers are used to represent the pressureforce exerted by foot on load sensors located in insoles. In case ofstanding, person's weight is determined based on the values of signalsF₁ and F₂ generated by piezoelectric transducers at the beginning ofstanding activity and after its termination. Apart from that, theimplementation of the method is similar to the one described in thepreceding example.

Devices 6 (FIG. 2) and 12 (FIG. 6), as well as portions thereof, can beaccommodated in insole 1 alongside with corresponding load sensors. Thedevices are energized by battery 10 which can be represented by arechargeable battery. Additionally, the device can comprise a circuitfor battery recharging while walking or running, as shown in the exampleof device 12 (see FIG. 6). Such a recharging circuit includes diodes 16,one for each piezoelectric transducer 13-15, storage capacitor 17, andthyristor 18 whose control input is coupled to input/output port L9 ofmicrocontroller 9. One end of each diode 16 is connected tocorresponding piezoelectric transducer 13-15, while all other ends arejoined and connected to capacitor 17. In the process of recharging,microcontroller 9 switches off the registration mode of signalsgenerated by foot pressure on piezoelectric transducers, sending saidsignals through diodes 16 to storage capacitor 17. In this mode,microcontroller 9 opens thyristor 18, thereby connecting chargedcapacitor 17 to battery 10. Thus, when a person is walking or running inshoes with device 12 and piezoelectric transducers 13-15 mounted in shoeinsoles, battery 10 is recharged.

The method according to the present invention enables a more accurateassessment of type and duration of human motor activity and a moreprecise calculation of person's motor stress throughout the day, withthe type of motor activity and person's weight, including additionallycarried weight, taken into account.

Moreover, the data registered by load sensors mounted in insoles, asdescribed above, may also be used to detect the defects of person'smusculoskeletal system, flat footedness, as well as to determine theslope of travel surface and its hardness, degree of comfort of footwearworn, identification of gait specific for a person, etc. The method alsoenables a continuous monitoring of traveling pace, motion speed andacceleration, covered distance, and duration of travel.

What is claimed is:
 1. A method of monitoring motor stress and weight ofa person, the method comprising: registering signals from load sensorsdisposed in shoe insoles of the person, wherein each insole has a firstload sensor disposed in a heel region of an insole and a second loadsensor disposed in a toe region of the insole; determining a “walking”,“running” and “standing” type of the motor stress of the person based ontime relationship between signals from the load sensors in each insole;and determining the weight of the person and additional weight carriedby the person based on the type of the motor stress.
 2. The method ofclaim 1, wherein the type of the motor stress is determined as “walking”if (i) the signals from the load sensors in the insoles exhibit periodicvariations of values and (ii) the signals from the load sensors fromdifferent insoles partially overlap in time.
 3. The method of claim 1,wherein the type of the motor stress is determined as “running” if (i)the signals from the load sensors in the insoles exhibit periodicvariations of values and (ii) the signals from the load sensors fromdifferent insoles do not overlap in time.
 4. The method of claim 1,wherein the type of the motor stress is determined as “standing” if (i)the signals from the load sensors in the insoles exceed a predeterminedvalue and (ii) the signals from different insoles overlap in time. 5.The method of claim 1, wherein the weight of the person and theadditional weight at standing are determined as:P=K _(S) ·F, wherein: K_(S) is a calibration factor determined for aperson of a known weight at standing; F is a mean value of a footpressure force at standing, wherein:F=(F _(1max) +F _(2max))/2; wherein: F_(1max) is a maximum value ofsummarized foot pressure forces registered by the first and second loadsensors of one insole; and F_(2max) is the maximum value of summarizedfoot pressure forces registered by the first and second load sensors ofthe other insole.
 6. The method of claim 1, further comprising:providing in the shoe insoles additional load sensors disposed betweenthe first load sensor and the second load sensor; and using signals fromthe additional load sensors together with the signals from the first andsecond load.
 7. A system for monitoring motor stress of a person,comprising: two insoles each having a first load sensor disposed in aheel region of an insole and a second load sensor disposed in a toeregion of the insole; a transmitter adapted to transmit in a digitalform signals from the load sensors to an external processing unit; andthe external processing unit adapted for determining weight of theperson, a value of additional weight carried by the person, or a valueof the motor stress of the person based on: time relationship betweenthe signals from the load sensors in each insole; and a “walking”,“running” and “standing” type of the motor stress of the person.
 8. Thesystem of claim 7, wherein each of the insoles comprises at least oneload sensor disposed between the first and second load sensors.